US20150168523A1 - Mri apparatus - Google Patents
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- US20150168523A1 US20150168523A1 US14/566,186 US201414566186A US2015168523A1 US 20150168523 A1 US20150168523 A1 US 20150168523A1 US 201414566186 A US201414566186 A US 201414566186A US 2015168523 A1 US2015168523 A1 US 2015168523A1
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- 238000012937 correction Methods 0.000 claims abstract description 50
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
- G01R33/48—NMR imaging systems
- G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
- G01R33/48—NMR imaging systems
- G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
- G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
- G01R33/565—Correction of image distortions, e.g. due to magnetic field inhomogeneities
- G01R33/5659—Correction of image distortions, e.g. due to magnetic field inhomogeneities caused by a distortion of the RF magnetic field, e.g. spatial inhomogeneities of the RF magnetic field
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
- G01R33/48—NMR imaging systems
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
- A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/288—Provisions within MR facilities for enhancing safety during MR, e.g. reduction of the specific absorption rate [SAR], detection of ferromagnetic objects in the scanner room
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
- G01R33/48—NMR imaging systems
- G01R33/58—Calibration of imaging systems, e.g. using test probes, Phantoms; Calibration objects or fiducial markers such as active or passive RF coils surrounding an MR active material
- G01R33/583—Calibration of signal excitation or detection systems, e.g. for optimal RF excitation power or frequency
Abstract
Description
- This application is based upon and claims the benefit of priority from Japanese Patent Application No. 2013-259488, filed on Dec. 16, 2013, the entire contents of which are incorporated herein by reference.
- An exemplary embodiment of the present invention relates to an MRI apparatus.
- In recent years, medical imaging apparatuses (hereinafter referred to as modality apparatuses), which can collect various information about a patient less invasively, have become indispensable in health-care settings. Among others, a magnetic resonance imaging (MRI) apparatus, which involves no radiation exposure and surpasses other modality apparatus in tissue contrast resolution, has come to be used in many medical institutions. The MRI apparatus is an imaging apparatus which excites nuclear spins of a patient placed in a static magnetic field with radio frequency (RF) pulses at Larmor frequency and thereby generates an image by reconstructing a magnetic resonance signal generated from the patient as a result of the excitation. To acquire a high-contrast image with an MRI apparatus, it is necessary to tilt the nuclear spins of the patient at a desired angle by application of the radio frequency pulses. The tilt is referred to as a flip angle and magnitude of the radio frequency pulse is expressed by the flip angle. That is, to acquire a high-contrast image, accurate radio frequency pulses need to be outputted from the MRI apparatus.
- The radio frequency pulses applied by the MRI apparatus is used as energy to give a tilt to the nuclear spins and other part is used as thermal energy to heat the patient and raise temperature of the patient. Thus, in the use of the MRI apparatus, from the standpoint of safety, a specific absorption ratio (SAR) has been defined as energy absorbed per unit mass of the patient and an upper limit of SAR, i.e., a safety standard value of SAR, has been prescribed as an IEC (International Electrotechnical Commission) standard (IEC 60601-2-33). More specifically, SAR (unit: W/kg) is defined as energy of the radio frequency pulses absorbed by 1 kg of living tissue, and upper limits of average SAR over arbitrary 10 seconds and average SAR over the most recent 6 minutes have been prescribed for each imaging site such as the whole body or the head. In order to carry out imaging such that the SAR will satisfy the safety standard value, the radio frequency pulses applied to the patient have to be accurate.
- Thus, an MRI apparatus is provided which predicts an SAR value based on imaging conditions and optimizes a sequence of imaging protocols so as to optimize the safety standard value.
- However, to carry out SAR-based safety management strictly, it is necessary to calculate the SAR value accurately. Thus, an MRI apparatus is provided which accurately calculates the SAR by directly measuring an electric current flowing through a transmitter coil by means of a scan performed prior to an examination of the patient and known as a prescan and calculating electric power used on the patient, based on the measured electric current. Furthermore, an MRI apparatus is provided which calculates an amount of power consumption from coefficients of a region, bed position, or the like by taking into consideration an amount of loss of the radio frequency pulses actually emitted to the patient, predicts the SAR value based on the calculated value, and thereby modifies imaging conditions.
- In this way, techniques are provided which accurately calculate SAR values by calculating the energy emitted to the patient.
- The techniques described above can calculate more accurate SAR values and strictly carry out SAR-based safety management. However, it is not known whether or not the radio frequency pulses are outputted as set out in imaging conditions, and if radio frequency pulses actually outputted are much stronger than the setting, the SAR value increases greatly, which could have resulted in a need to change the set imaging conditions. Also, even if the SAR value is measured accurately, there is a problem in that desired image contrast is not available if the radio frequency pulses are not applied at set power.
- Radio frequency pulses are outputted in a pulse manner multiple times in one examination and the outputted radio frequency pulses fluctuate in real time due to heating, load changes, aging degradation, and the like of elements used in an amplifier and transmitter coil and the like of a radio frequency pulse transmission circuit. That is, actual output could deviate in real time from radio frequency pulse output expected at a time of imaging condition setting. Such deviation could cause imaging to be performed at an output higher than predicted SAR value, requiring time and effort to change the set imaging conditions, or could cause imaging to be performed at an output lower than set radio frequency pulses, making it impossible to obtain desired image contrast. Consequently, in an examination using an MRI apparatus, it is necessary that the SAR value is measured correctly and that the radio frequency pulses are applied to the patient at an output as set out in imaging conditions.
- Thus, there is a demand for an MRI apparatus which can apply more accurate radio frequency pulses to the patient.
- In the accompanying drawings:
-
FIG. 1 is a conceptual configuration diagram showing an example of the MRI apparatus according to the exemplary embodiment; -
FIG. 2 is a functional block diagram showing a functional configuration example of a first embodiment of the MRI apparatus according to the exemplary embodiment; -
FIG. 3 is a diagram describing input/output characteristics of the transmitter unit of the MRI apparatus according to the exemplary embodiment; -
FIG. 4 is a flowchart showing an operation example of the first embodiment of the MRI apparatus according to the exemplary embodiment; -
FIG. 5 is a diagram describing a possible output timing of a corrective radio frequency pulse in a pulse sequence of the SE method on the MRI apparatus according to the exemplary embodiment. -
FIGS. 6A to 6C are diagrams describing a first corrective radio frequency pulse on the MRI apparatus according to the exemplary embodiment; -
FIGS. 7A to 7C are diagrams describing a second corrective radio frequency pulse on the MRI apparatus according to the exemplary embodiment; -
FIG. 8 is a diagram describing a possible output timing of a corrective radio frequency pulse in a pulse sequence of the GRE method on the MRI apparatus according to the exemplary embodiment; -
FIGS. 9A and 9B are diagrams describing a variation of the first corrective radio frequency pulse on the MRI apparatus according to the exemplary embodiment; -
FIG. 10 is a diagram describing a method used by the MRI apparatus according to the exemplary embodiment to calculate input/output characteristics based on imaging radio frequency pulses; -
FIG. 11 is a functional block diagram showing a functional configuration example of a second embodiment of the MRI apparatus according to the exemplary embodiment of the present invention; and -
FIG. 12 is a flowchart showing an operation example of the second embodiment of the MRI apparatus according to the exemplary embodiment. - An MRI apparatus according to an exemplary embodiment of the present invention will be described below with reference to the accompanying drawings.
- To solve the above-described problems, an MRI apparatus comprising, a generating unit configured to generate radio frequency pulses applied in a pulse sequence; a sequence control unit configured to apply a radio frequency pulse related to acquisition of an image signal and a corrective radio frequency pulse during execution of one TR of a pulse sequence; and a calculation unit configured to measure the corrective radio frequency pulse and calculates a correction value of the radio frequency pulse, wherein based on the correction value, the generating unit corrects a radio frequency pulse related to acquisition of an image signal to be applied during a following TR later than a TR during which the corrective radio frequency pulse is measured.
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FIG. 1 is a conceptual configuration diagram showing an example of the MRI apparatus according to the exemplary embodiment. As shown inFIG. 1 , theMRI apparatus 10 is largely made up of animaging system 11 and acontrol system 12. - The
imaging system 11 includes astatic magnet 21, agradient coil 22, agradient power supply 23, abed 24, abed control unit 25, atransmitter coil 26, atransmitter unit 27,receiver coils 28 a to 28 e, apickup coil 28 f, areceiver unit 29, awave detector 30, and a sequence control unit 40 (a sequence controller). - The
static magnet 21 is formed into a hollow cylindrical shape in outermost part of a gantry (not shown) and configured to generate a uniform static magnetic field in an internal space. As thestatic magnet 21, a permanent magnet or superconductive magnet is used, for example. - The
gradient coil 22, which is formed into a hollow cylindrical shape, is placed inside thestatic magnet 21. Thegradient coil 22 is formed by a combination of an Xch coil 22 x, Ych coil 22 y, and Zch coil 22 z (not shown) corresponding, respectively, to X, Y, and Z axes orthogonal to one another. Being supplied with electric currents individually from thegradient power supply 23 described later, the three coils 22 x, 22 y, and 22 z generate gradient magnetic fields whose magnetic field intensities change along the X, Y, and Z axes, respectively. Note that the Z axis coincides in direction with the static magnetic field. - The gradient magnetic fields generated on the X, Y, and Z axes by the
gradient coil 22 correspond, for example, to a readout gradient magnetic field Gr, a phase encoding gradient magnetic field Gp, and a slice selection gradient magnetic field Gs, respectively. The readout gradient magnetic field Gr is used to change a frequency of an MR (magnetic resonance) signal according to spatial position. The phase encoding gradient magnetic field Gp is used to change a phase of the MR signal according to the spatial position. The slice selection gradient magnetic field Gs is used to determine an imaging section as desired. - The
gradient power supply 23 supplies an electric current to thegradient coil 22 based on pulse sequence execution data sent from thesequence control unit 40. - The
bed 24 includes atable top 24 a on which a patient P is mounted. Thebed 24 inserts thetable top 24 a with the patient P mounted thereon into a cavity (bore), which is an imaging area of thegradient coil 22, under the control of thebed control unit 25 described later. Normally, thebed 24 is installed such that a longitudinal direction thereof will be parallel to a center axis of thestatic magnet 21. - The
bed control unit 25 moves the table top 24 a in longitudinal and vertical directions by driving thebed 24 under the control of thesequence control unit 40. - The
transmitter coil 26, which is placed on an inner side of thegradient coil 22, generates radio frequency pulses by being supplied with electric power from thetransmitter unit 27. - Based on a time chart called a pulse sequence sent from the
sequence control unit 40, thetransmitter unit 27 controls electric power supplied to thetransmitter coil 26. A power control configuration of thetransmitter unit 27 will be described later. - The receiver coils 28 a to 28 e, which are placed on the inner side of the
gradient coil 22, receive MR signals emitted from the patient P under influence of an RF magnetic field. Each of the receiver coils 28 a to 28 e is an array coil made up of plural coil elements which receive the respective magnetic resonance signals emitted from the patient P and outputs the received MR signals to thereceiver unit 29 when the MR signals are received by the respective coil elements. - The
receiver coil 28 a is a head coil mounted around the head of the patient P. Also, the receiver coils 28 b and 128 c are spine coils placed between the spine of the patient P and the table top 124 a. Also, the receiver coils 28 d and 28 e are abdominal coils mounted around the abdomen of the patient P. Also, theMRI apparatus 10 may be equipped with a combined transmitter-receiver coil. - The
pickup coil 28 f is placed inside the bore or on an outer side of the gantry for thegradient coil 22 and adapted to receive corrective radio frequency pulses outputted from thetransmitter coil 26. When thepickup coil 28 f receives the corrective radio frequency pulses, a resulting signal is detected by thewave detector 30. The signal detected by thewave detector 30 is converted into a digital signal by an analog-to-digital converter (not shown) and is transmitted to thecontrol system 12 via thesequence control unit 40. Using the acquired data, thecontrol system 12 corrects the radio frequency pulses outputted from thetransmitter unit 27 and calculates the SAR value. - Based on a pulse sequence sent from the
sequence control unit 40, thereceiver unit 29 generates MR signal data from the receiving coils 28 a to 28 e. - The
sequence control unit 40 is connected with thegradient power supply 23,bed control unit 25,transmitter unit 27,receiver unit 29,wave detector 30, andcontrol system 12. Thesequence control unit 40 includes a processor (not shown) such as a CPU (central processing unit) and memory, and stores control information needed to drive thegradient power supply 23,bed control unit 25,transmitter unit 27,receiver unit 29, andwave detector 30 including, for example, a pulse sequence describing operational control information such as intensity, application duration, and application timing of a pulsed current to be applied to thegradient power supply 23. - Also, the
sequence control unit 40 drives thebed control unit 25 according to a stored predetermined pulse sequence and thereby moves the table top 24 a forward and backward in a Z direction with respect to the gantry. Furthermore, thesequence control unit 40 drives thegradient power supply 23,transmitter unit 27,receiver unit 29, andwave detector 30 according to a stored predetermined pulse sequence and thereby controls generation and detection of an X-axis gradient magnetic field Gx, Y-axis gradient magnetic field Gy, and Z-axis gradient magnetic field Gz as well as radio frequency pulses in the gantry. - The
control system 12 performs overall control of theMRI apparatus 10, data collection, and image reconstruction as well as calculation and correction of the input/output characteristics of thetransmitter unit 27. Thecontrol system 12 includes aninterface unit 41, adata collection unit 42,data processing unit 43,storage unit 44,display unit 45,input unit 46, andcontrol unit 47. - The
interface unit 41 is connected to thegradient power supply 23,bed control unit 25,transmitter unit 27,receiver unit 29, andwave detector 30 of theimaging system 11 via thesequence control unit 40 and adapted to control input and output of signals exchanged between the connected components and thecontrol system 12. - The
data collection unit 42 collects MR signal data transmitted from thereceiver unit 29 via theinterface unit 41. Upon collecting the MR signal data, thedata collection unit 42 stores the collected MR signal data in thestorage unit 44. - The
data processing unit 43 generates spectrum data or image data of a desired nuclear spin in the patient P by applying postprocessing, i.e., a reconstruction process such as a Fourier transform, to the MR signal data stored in thestorage unit 44. Also, when a locator image is captured in a prescan or the like, thedata processing unit 43 generates profile data for each of the plural element coils of the receiving coils 28 a to 28 e based on the MR signal received by the element coil, the profile data representing a distribution of MR signals in an arranging direction of the element coil. Then, thedata processing unit 43 stores various generated data in thestorage unit 44. - The
display unit 45 displays various information, such as spectrum data or image data, generated bydata processing unit 43. As thedisplay unit 45, a display device such as a liquid crystal display can be used. - An
input unit 46 accepts various actions and information inputs from an operator. As theinput unit 46, a pointing device such as a mouse or track ball, a selecting device such as a mode selector switch, or an input device such as a keyboard can be used as appropriate. - The
control unit 47 measures input/output characteristics of thetransmitter unit 27 based on electric power inputted in order for thetransmitter unit 27 to generate radio frequency pulses and on electric power outputted to thetransmitter coil 26, and thereby calculates a correction value used to control the output of radio frequency pulses for measurement at a next repetition time (TR). The TR is a time interval from the time when a radio frequency pulse is applied to excite the patient P to the time when a radio frequency pulse is applied to excite the patient P next. Furthermore, based on a signal detected by thewave detector 30 by measuring thepickup coil 28 f adapted to receive an RF receive signal, thecontrol unit 47 calculates correction values of electric power supplied to thetransmitter unit 27 andtransmitter coil 26. Also, thecontrol unit 47 includes an CPU, memory, and the like not illustrated and comprehensively controls theMRI apparatus 10 by controlling the calculation of the SAR value and the components described above. - For each patient P and each imaging protocol, the
storage unit 44 stores the imaging conditions necessary for generation of a pulse sequence, the MR signal data collected by thedata collection unit 42, and the image data generated and SAR value calculated by thedata processing unit 43 as well as correction values. -
FIG. 2 is a functional block diagram showing a functional configuration example of a first embodiment of theMRI apparatus 10 according to the exemplary embodiment. As shown inFIG. 2 , theMRI apparatus 10 includes thetransmitter coil 26, anamplifier unit 272, agenerating unit 275, awave detector 277, asequence control unit 40, an imagingcondition storage unit 441, and acalculation unit 471. Theamplifier unit 272 includes asignal amplifier 271 and adirectional coupler 273. Of these, thecalculation unit 471 is a function implemented when the CPU of thecontrol unit 47 included in thecontrol system 12 executes a program stored in thestorage unit 44. - The imaging
condition storage unit 441 stores imaging conditions which prescribe a pulse sequence. The imaging conditions define a type of pulse sequence used to transmit radio frequency pulses and the like, conditions under which the radio frequency pulses are transmitted, and conditions under which MR signals are collected from the patient P. Examples of the imaging conditions include the imaging area which provides positional information in an imaging space, flip angle, repetition time (TR), number of slices, imaging site, type of pulse sequence such as an SE (Spin Echo) method or parallel imaging. The imaging site is a region of the patient P, such as the head, chest, or abdomen whose images are to be produced in the imaging area. Examples of the pulse sequence will be described later. - The generating
unit 275 generates radio frequency pulses to be applied in the pulse sequence. Radio frequency pulses of a predetermined waveform are generated from reference radio frequency pulses (an RF carrier wave) according to conditions prescribed for the pulse sequence. Also, based on a correction value, the generatingunit 275 corrects a radio frequency pulse related to acquisition of an image signal to be applied during a TR in a stage later than a TR during which the corrective radio frequency pulse is measured. The radio frequency pulses generated by the generatingunit 275 can be either corrective radio frequency pulses for use to correct input/output characteristics such as gain and linearity of the transmitter unit 27 (hereinafter referred to simply as correction of the transmitter unit 27) or imaging radio frequency pulses for use to take images of the patient P. The radio frequency pulses generated will be described later. - The
signal amplifier 271 amplifies the radio frequency pulses generated by the generatingunit 275, and gives the radio frequency pulses to thetransmitter coil 26 via thedirectional coupler 273. The amplified radio frequency pulses are transmitted to thetransmitter coil 26. - The
directional coupler 273 is a radio frequency device adapted to branch the radio frequency pulses transmitted from thesignal amplifier 271 to thetransmitter coil 26 by attenuating the radio frequency pulses using a predetermined degree of coupling (coupling coefficient). An output signal of thedirectional coupler 273 is detected by thewave detector 277 on an MR signal processing board and converted into a digital signal by an analog-to-digital converter (not shown). Data resulting from the conversion carried out by the analog-to-digital converter is transmitted to thecontrol system 12 via thesequence control unit 40. Thecontrol system 12 performs correction of thetransmitter unit 27 and calculates the SAR value using the acquired data. - The
calculation unit 471 measures the corrective radio frequency pulses and calculates correction values of the radio frequency pulses. Thecalculation unit 471 receives output data of the analog-to-digital converter and calculates correction values of thetransmitter unit 27. A method used by thecalculation unit 471 to calculate the correction values will be described later. - The
sequence control unit 40 applies a radio frequency pulse related to acquisition of an image signal and a corrective radio frequency pulse during execution of one TR of a pulse sequence. Based on input/output characteristics calculated by thecalculation unit 471, thesequence control unit 40 adjusts a magnitude of the radio frequency pulses to be generated by the generatingunit 275 or input power of thesignal amplifier 271 in order to generate radio frequency pulses to be outputted during TRs later than the TR during which input/output characteristics are calculated. -
FIG. 3 is a diagram describing input/output characteristics of thetransmitter unit 27 of theMRI apparatus 10 according to the exemplary embodiment. Input/output characteristics of thetransmitter unit 27 fluctuate due to heating, load changes, aging degradation, and the like of elements used in thesignal amplifier 271 andtransmitter coil 26 of a radio frequency pulse transmission circuit. Also, the electric power inputted to thetransmitter coil 26 from thesignal amplifier 271 varies with a balance between resistance values of thesignal amplifier 271 andtransmitter coil 26 and the radio frequency pulses actually transmitted may differ from output set out in imaging conditions. - The solid line in
FIG. 3 represents an example of input/output characteristics of thetransmitter unit 27 measured at a time of installation of theMRI apparatus 10. Input/output characteristic A indicated by alternate long and short dash lines and input/output characteristic B indicated by a broken line inFIG. 3 are examples of the input/output characteristics of thetransmitter unit 27 in theMRI apparatus 10 after actual operation. According to input/output characteristic A, at the input power of thesignal amplifier 271, output power A detected by thewave detector 277 is larger than predicted output power estimated from the input/output characteristic at the time of installation. On the other hand, according to input/output characteristic B, at the input power of thesignal amplifier 271, output power B detected by thewave detector 277 is smaller than the predicted output power estimated from the input/output characteristic at the time of installation. Also, regarding input/output characteristic B, it can be seen that the larger the input power, the smaller a slope, resulting in an output diverging greatly from the input/output characteristic at the time of installation. - The changes in the input/output characteristics of the
transmitter unit 27 shown inFIG. 3 are affected by heating of elements, changes in resistance values, and the like of thetransmitter unit 27 andtransmitter coil 26. Generally, in imaging on the MRI apparatus, before images start to be captured in earnest, some settings are calibrated such that imaging can be carried out properly. This calibration is referred to as a prescan. In the prescan, a sequence for calculating a center frequency of the radio frequency pulses is performed, and output of the radio frequency pulses is corrected before each examination. However, it is conceivable that changes such as shown inFIG. 3 take place moment by moment during operation of the MRI apparatus with fluctuations occurring every TR. - Thus, the
MRI apparatus 10 according to the present invention measures fluctuating input/output characteristics of thetransmitter unit 27 in real time and accurately outputs radio frequency pulses according to imaging conditions. -
FIG. 4 is a flowchart showing an operation example of the first embodiment of theMRI apparatus 10 according to the exemplary embodiment. - In ST101 of
FIG. 4 , the generatingunit 275 generates a corrective radio frequency pulse. - In ST103, the generated radio frequency pulse is outputted to the
transmitter coil 26 via thesignal amplifier 271. - In ST105, the signal outputted to the
transmitter coil 26 is attenuated by thedirectional coupler 273 and a resulting output signal is measured by thewave detector 277 on the MR signal processing board. - In ST107, the measured signal is sent to the
calculation unit 471 via thesequence control unit 40 and the input/output characteristics of thetransmitter unit 27 are measured based on the measured signal to calculate a correction value. - In ST109, based on the calculated correction value, the
calculation unit 471 calculates a numeric value used to correct a magnitude of the reference radio frequency pulse for use by the generatingunit 275 in generating the imaging radio frequency pulse. Also, based on the calculated correction value, the input power of thesignal amplifier 271 is adjusted, and thetransmitter unit 27 outputs the corrected imaging radio frequency pulse. -
FIG. 5 is a diagram describing a possible output timing of a corrective radio frequency pulse in a pulse sequence of the SE method on theMRI apparatus 10 according to the exemplary embodiment. The chart inFIG. 5 shows a pulse sequence based on the SE (Spin Echo) method. The chart shows, from top down, radio frequency pulses, a slice selection gradient magnetic field Gs, a phase encoding gradient magnetic field Gp, a readout gradient magnetic field Gr, and an MR signal, with the arrow at the bottom representing time. The SE method uses a signal which decays as an FID (Free Induction Decay) signal after an excitation pulse is given and then returns again as an echo. Specifically, as shown inFIG. 5 , if the time until an echo returns after application of an excitation pulse with a flip angle of 90 degrees is designated as an echo time (TE), a refocus pulse with a flip angle of 180 degrees is applied after a time equal to half (TE/2) the echo time. By the application of the refocus pulse, transverse magnetization which has diffused converges, and an echo signal is produced after a time of TE and received by the receiving coils 28. The SE method is an imaging method which can cancel out influence of nonuniformity of a magnetic field, and thus even if static magnetic field is slightly nonuniform or there is a substance (substance with high magnetic susceptibility) which changes a magnetic field, the method can minimize the influence thereof. - The interval TR indicated by an arrow in
FIG. 5 is the repetition time. That is, in the SE method, the time between a pulse with a flip angle of 90 degrees and a next flip angle with a flip angle of 90 degrees is the TR. One examination is made up of plural imaging protocols, and one imaging protocol includes plural TRs. In one imaging protocol, the TR is repeated as many times as needed to reconstruct an image. - Region A in
FIG. 5 shows an example of timing to output a corrective radio frequency pulse in a sequence according to the SE method. In this way, thesequence control unit 40 adds a corrective radio frequency pulse to part of a pulse sequence. In the pulse sequence, the corrective radio frequency pulse needs to be outputted at such a timing and output conditions that do not affect MR signals collected for image reconstruction. That is, in the SE method, a zone of influence can be moved out of an imaging region by applying a gradient magnetic field pulse with a same timing as region A. Also, the zone of influence can be moved out of the imaging region by establishing such an output condition that a frequency of a corrective radio frequency signal will not be included in an imaging band. The timing to output the corrective radio frequency pulse comes between the time immediately after MR signal collection for image reconstruction is completed and the time when a next TR starts, for example, as shown in region A ofFIG. 5 . When the corrective radio frequency pulse is applied at the timing described above, if a duration of the TR is made longer than when no corrective radio frequency pulse is applied, the corrective radio frequency pulse can be applied without affecting imaging in the next TR. Also, in applying the corrective radio frequency pulse, if portions irrelevant to imaging are slice-selected, influence of the corrective radio frequency pulse can be moved out of the imaging region, making it possible to apply the corrective radio frequency pulse without extending the TR. For example, in imaging the abdomen, if a gradient magnetic field is applied simultaneously such that portions such as the legs irrelevant to imaging will be selected at the timing of application of the corrective radio frequency pulse, the corrective radio frequency pulse can be applied without affecting imaging of imaging sites in the abdomen. -
FIGS. 6A to 6C are diagrams describing a first corrective radio frequency pulse on theMRI apparatus 10 according to the exemplary embodiment.FIG. 6A illustrates a triangular wave as an example of the corrective radio frequency pulse generated by the generatingunit 275. The ordinate represents electric power and the abscissa represents time. The triangular wave is outputted with an amplitude large enough to include output of an imaging radio frequency pulse. For example, the SE method illustrated inFIG. 5 outputs radio frequency pulses which contain electric power corresponding to RF outputs of at least an excitation pulse with a flip angle of 90 degrees and a refocus pulse with a flip angle of 180 degrees as imaging radio frequency pulses. Specifically, a triangular wave is outputted to supply peak power higher than the electric power supplied to thetransmitter coil 26 when a radio frequency pulse with a flip angle of 180 degrees is outputted as a corrective radio frequency pulse. As shown inFIG. 6A , electric power outputted by the generatingunit 275 at plural points of the outputted triangular wave and output power detected by thewave detector 277 are sampled, and the input/output characteristics of thetransmitter unit 27 are measured. - Note that since output of the corrective radio frequency pulse is completed within a time as short as ten-odd ms (milliseconds), measurements can be taken in a very short time even in view of the fact that a TR interval is 1000 ms to 100 ms. Therefore, even if the patient P is irradiated with such a corrective radio frequency pulse, temperature of the patient P does not rise rapidly and the SAR value does not fluctuate much.
-
FIG. 6B is a graph showing an input/output characteristic of thetransmitter unit 27 measured from the triangular wave illustrated by example inFIG. 6A . The ordinate represents output power and the abscissa represents input power. The solid line is a graph of output power detected by thewave detector 277 and the broken line is a graph based on output power expected from conditions set out as imaging conditions in relation to the inputted triangular wave. The graph indicated by the solid line inFIG. 6B shows an example in which output power is lower than input power, with the input power diverging greatly from predicted output in a neighborhood of a 90-degree pulse inFIG. 6A . The arrow inFIG. 6B indicates a correction value calculated by thecalculation unit 471 from a difference between power outputted actually and output power predicted from input power. - As with
FIG. 6B ,FIG. 6C is a graph showing an input/output characteristic of thetransmitter unit 27 measured from the triangular wave illustrated by example inFIG. 6A . UnlikeFIG. 6B ,FIG. 6C shows an example in which output power is higher than input power, with the output power growing larger than predicted output with increases in input power. As withFIG. 6B , the arrow inFIG. 6C indicates a correction value calculated by thecalculation unit 471 from a difference between power outputted actually and output power predicted from input power. -
FIGS. 7A to 7C are diagrams describing a second corrective radio frequency pulse on theMRI apparatus 10 according to the exemplary embodiment. WhereasFIG. 6A shows an example in which a triangular wave is used as a corrective radio frequency pulse,FIG. 7A shows an example in which a sinc wave is used. The ordinate represents electric power and the abscissa represents time. As with the triangular wave inFIG. 6A , the sinc wave includes output of an imaging radio frequency pulse. Electric power outputted by the generatingunit 275 at plural points, and output power detected by thewave detector 277 are sampled, and the input/output characteristics of thetransmitter unit 27 are measured. - In
FIG. 7B , the solid line indicates the sinc wave detected by thewave detector 277 and the broken line indicates the sinc wave outputted by the generatingunit 275. In the example ofFIG. 7B , in the portion with a large amplitude, the sinc wave actually outputted has a small amplitude. In this way, thecalculation unit 471 calculates a correction value from a difference between predicted sinc wave and actually detected sinc wave. -
FIG. 7C is a graph showing an input/output characteristic of thetransmitter unit 27 measured from the sinc wave shown inFIG. 7A . As withFIG. 7B , the solid line indicates output power detected by thewave detector 277 and the broken line indicates output power outputted to thetransmitter coil 26. As is clear fromFIG. 7B , it can be seen that there is a large divergence between predicted output and actual output when the amplitude is large, i.e., when the electric power is high. - The
MRI apparatus 10 described above outputs a corrective radio frequency pulse at such a timing that does not affect image reconstruction in one TR, calculates the input/output characteristics of thetransmitter unit 27 from an actually outputted signal, and thereby corrects imaging radio frequency pulses in next and subsequent TRs. By measuring the input/output characteristics of thetransmitter unit 27 in every TR in this way, it is possible to make corrections in thetransmitter unit 27 in real time, output radio frequency pulses more faithful to imaging conditions, and thereby improve image contrast and carry out SAR-based safety management strictly. - Although the application timing of a corrective radio frequency pulse according to the SE method has been described in
FIG. 5 by way of example, available timing for application of a corrective radio frequency pulse is not limited to this. -
FIG. 8 is a diagram describing a possible output timing of a corrective radio frequency pulse in a pulse sequence of the GRE method on theMRI apparatus 10 according to the exemplary embodiment. The GRE (Gradient Recalled Echo) method is a technique for obtaining an echo signal with spins aligned in phase by reversing a gradient magnetic field in a direction of a readout gradient magnetic field Gr once after excitation of spins through emission of radio frequency pulses and then applying a gradient magnetic field again in a correct direction. If a readout gradient magnetic field Gr is provided in advance and then reversed, the spins advanced in phase become slow and conversely the spins delayed in phase become fast, and consequently a diffused signal converges again to produce an echo signal. Since the method does not need to use a flip angle of 90 degrees, a recovery time can be reduced and imaging can be carried out faster than the SE method. -
FIG. 8 shows a pulse sequence based on the GRE method. As withFIG. 5 ,FIG. 8 shows, from top down, radio frequency pulses, a slice selection gradient magnetic field Gs, a phase encoding gradient magnetic field Gp, a readout gradient magnetic field Gr, and an MR signal with the arrow at the bottom representing time. Also, the interval TR indicated by an arrow inFIG. 8 is a repetition time (TR). As described above, unlike the SE method inFIG. 5 , the GRE method requires one excitation pulse and does not require a pulse with a flip angle of 90 degrees as indicated by α° inFIG. 8 . Furthermore, since a refocus pulse with a flip angle of 180 degrees is not used, the influence of nonuniformity of a static magnetic field cannot be cancelled out. Thus, a method is provided which carries out imaging at high speed using a method for erasing remaining magnetization by giving a pulse called a spoiler after signal collection. With a pulse sequence of the GRE method described above, by outputting a corrective radio frequency pulse at the output timing of the spoiler pulse as shown in region B ofFIG. 8 , the input/output characteristics of thetransmitter unit 27 can be measured without affecting a next sequence. - In the examples of
FIGS. 5 and 8 , sampling is done multiple times in one TR, but sampling frequency is not limited as long as sampling is done one or more times. Also, regarding sizes of corrective radio frequency pulses, pulses with a same pulse size may be outputted in respective TRs, pulses of different sizes may be outputted, or pulses may be outputted in such a manner that triangular and sinc waves are alternatively outputted for measurements. Furthermore, regarding correction timing, an acquired correction value may be reflected in an immediately succeeding TR or in a TR plural TRs after the TR in which the correction value is acquired. Also, an average value or median of correction values acquired over multiple TRs may be calculated and used to correct the radio frequency pulse. -
FIGS. 9A and 9B are diagrams describing a variation of the first corrective radio frequency pulse on theMRI apparatus 10 according to the exemplary embodiment.FIGS. 9A and 9B show an example in which the triangular wave shown in the example ofFIG. 6 is outputted in various sizes over different TRs. - The triangular wave indicated by a broken line in
FIG. 9A is a same one as isFIG. 6A . Each of the three triangular waves indicated by a solid line has a vertex at one of the sampling points of the triangular wave inFIG. 6A . The triangular waves are designated as triangular wave A, triangular wave B, and triangular wave C, starting from the left. -
FIG. 9B shows an example in which the triangular waves A to C indicated by solid lines are outputted in different TRs. In the example ofFIG. 9B , triangular wave A is outputted in TR1, triangular wave B is outputted in TR2, and triangular wave C is outputted in TR3, and triangular wave A is outputted again in TR4. InFIG. 9B , a correction value is calculated in each TR, and even though triangular waves of different sizes are outputted separately, a correction value is calculated for each triangular wave, such as a correction value of ±a in TR1, a correction value of ±b in TR2, correction value of ±c in TR3, and a correction value ±d in TR4. Also, the calculated correction value may be reflected in generating an imaging radio frequency pulse in a next TR. Furthermore, correction values acquired over plural TRs may be used to correct the radio frequency pulse outputted in any of TRs subsequent to the TRs in which the correction values are acquired. TakeFIG. 9B as an example, a correction value may be calculated from the correction values of ±a and ±b acquired in TR1 and TR2 and then output of a radio frequency pulse may be corrected in a subsequent TR, i.e., in TR3 or TR4. Sampling can be done multiple times on each triangular wave to measure the input/output characteristics of thetransmitter unit 27. Also, even if sampling is done at one point, a correction value can be calculated by predicting actual output of desired output from a difference between planned output and actual output. - In this way, by using a method which outputs plural radio frequency pulses differing in size, it is possible to apply a signal in a shorter time than when an ordinary triangular wave or sinc wave is used. Also, for example, if frequency of a triangular wave and the sinc wave is reduced, sampling can be done more frequently, making it possible to measure input/output characteristics more accurately. Furthermore, although a triangular wave inscribed in the triangular wave of
FIG. 6A is shown inFIG. 9 , triangular waves in a similarity relationship with each other may be outputted in different TRs. - A method for measuring the input/output characteristics of the
transmitter unit 27 by applying corrective radio frequency pulses in addition to imaging radio frequency pulses has been shown above. However, this is not restrictive, and imaging radio frequency pulses may be used as corrective radio frequency pulses. That is, as described above, even if corrective radio frequency pulses are not outputted in executing a pulse sequence, thecalculation unit 471 can calculate correction values by measuring the input/output characteristics of thetransmitter unit 27 based on the input power inputted to thetransmitter coil 26 by the generatingunit 275 and the output power detected by thewave detector 277 in relation to actual imaging radio frequency pulses. -
FIG. 10 is a diagram describing a method used by the MRI apparatus according to the exemplary embodiment to calculate input/output characteristics based on imaging radio frequency pulses. As withFIGS. 6 and 7 ,FIG. 10 is a graph showing an input/output characteristic of thetransmitter unit 27. The ordinate represents output power and the abscissa represents input power. The points represent output powers detected by thewave detector 277 in relation to a pulse with a flip angle of 90 degrees and a pulse with a flip angle of 180 degrees that are applied in in the SE method, respectively. The broken line represents a graph based on output power expected from conditions set out as imaging conditions. The alternate long and short dash lines show a graphic plot of a current input/output characteristic of thetransmitter unit 27 based on two points measured from the pulse with a flip angle of 90 degrees and the pulse with a flip angle of 180 degrees. Respective correction values can be calculated from the two points or even if only one of the two points is detected, a correction value in another output can be predicted from a calculated correction value. - In this way, the input/output characteristics of the
transmitter unit 27 are measured in each TR and accurate radio frequency pulses are applied, making it possible to carry out imaging under conditions extremely close to those set out as imaging conditions, improve image contrast, and increase accuracy of image reconstruction or image processing. Furthermore, since an accurate SAR value can be calculated in real time, imaging can be carried out in more efficient order and under more efficient imaging conditions. - Although a method for measuring the input/output characteristics of the
transmitter unit 27 by measuring input power and output power using the configuration of thetransmitter unit 27 has been described in the first embodiment, embodiments are not limited to this. In a second embodiment shown below, a method will be described which measures input/output characteristics of theMRI apparatus 10 based on a signal resulting from radio frequency pulses actually outputted from thetransmitter coil 26 and received by a pickup coil installed near the gantry or in the bore. -
FIG. 11 is a functional block diagram showing a functional configuration example of a second embodiment of theMRI apparatus 10 according to the exemplary embodiment of the present invention. The same components as those in the first embodiment are denoted by the same reference numerals as the corresponding components in the first embodiment. Components different from those inFIG. 2 will only be described below. - As shown in
FIG. 11 , theMRI apparatus 11 according to the second embodiment includes thepickup coil 28 f andwave detector 30 in addition to the components of the first embodiment. - The
pickup coil 28 f receives corrective radio frequency pulses outputted from thetransmitter coil 26. - The
wave detector 30 measures a voltage when a corrective radio frequency pulse is received by thepickup coil 28 f, and acquires an output voltage. The acquired output voltage is transmitted to thecalculation unit 471 via thesequence control unit 40. Thecalculation unit 471 calculates a correction value based on the acquired output voltage and the output voltage at which the corrective radio frequency pulse is transmitted to thetransmitter coil 26 by thecalculation unit 471. -
FIG. 12 is a flowchart showing an operation example of the second embodiment of theMRI apparatus 10 according to the exemplary embodiment. As withFIG. 10 , the same processes as those in the first embodiment are denoted by the same reference numerals as the corresponding processes in the first embodiment. Processes different from those inFIG. 4 will only be described below. - In ST151, the
pickup coil 28 f receives a corrective radio frequency pulse. - In ST153, the
wave detector 30 detects an output voltage. - In ST155, the
calculation unit 471 calculates the input/output characteristics ofMRI apparatus 10 from an input voltage inputted to thetransmitter coil 26 by the generatingunit 275 and an output voltage acquired by thewave detector 30, and corrects output of a next imaging radio frequency pulse. - Note that output timing of the corrective radio frequency pulse in the second embodiment is the same as the first embodiment.
- In this way, by measuring actually outputted radio frequency pulses using the
pickup coil 28 f installed in the bore or near the gantry, the second embodiment can measure the input/output characteristics of an entire transmitter circuit system of theMRI apparatus 10 including the output from thetransmitter coil 26 when compared to the first embodiment. That is, by directly measuring the radio frequency pulses applied to the patient P from thetransmitter coil 26, it is possible to make corrections by taking into consideration losses and load changes in thetransmitter coil 26. - While certain embodiments have been described, these embodiments have been presented by way of example only, and are not intended to limit the scope of the inventions. Indeed, the novel methods and systems described herein may be embodied in a variety of other forms; furthermore, various omissions, substitutions and changes in the form of the methods and systems described herein may be made without departing from the spirit of the inventions. The accompanying claims and their equivalents are intended to cover such forms or modifications as would fall within the scope and spirit of the inventions.
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